Phillip DiGiacomo1, Mackenzie Carlson1, Julian Maclaren1, Murat Aksoy1, Yi Wang2, Pascal Spincemaille2, Brian Burns3, Roland Bammer1, Brian Rutt1, and Michael Zeineh1
1Stanford University, Stanford, CA, United States, 2Cornell University, Ithaca, NY, United States, 3GE Healthcare, San Francisco, CA, United States
Synopsis
Recent literature
has shown the potential of high‐resolution quantitative susceptibility mapping
(QSM) with ultra‐high field (7T) MRI for investigating the
magnetostatic properties of brain structures
and disease pathology. Higher spatial resolutions, however, require longer
scans resulting in a higher likelihood of subject movement. Here, we apply a novel
prospective real-time optical motion tracking and correction system using a
camera integrated between the Tx and Rx coils of a commercial 7T head coil to
demonstrate the feasibility of acquiring high-resolution R2* and QSM images
robust to subject motion.
Introduction
Quantitative
susceptibility mapping (QSM) has shown potential in elucidating novel insights
into the pathology associated with traumatic brain injury, multiple sclerosis, Alzheimer’s
disease, and other diseases of the brain. Because susceptibility‐related frequency
differences scale linearly with field strength, and noise in the GRE phase
scales inversely proportional to the signal magnitude, performing QSM on
ultra-high-field (7T) MR systems may facilitate further discoveries. However, addressing motion artifact is a
pivotal step in translating QSM to 7T systems. Subject motion can cause spurious
phase fluctuations as well as image shifts that generate inconsistencies between the measured field and the bulk magnetic susceptibility of the
underlying tissue. Prior work has
shown that prospective motion correction (PMC) can provide improved
quantitative susceptibility maps,1 but this work used large bore-mounted cameras, limiting
line-of-sight on systems that use local closed-shell transmit head coils such
as the Nova 7T head coil. Our prior work2 implemented an optical prospective
motion correction system at 7T with a coil-integrated camera with line-of-sight
to a marker placed on the subject’s forehead which addresses this issue. The
goal of the present study is to test this fully integrated optical PMC system
on high-resolution QSM at 7T. This is expected to enable more widespread use of
QSM at 7T, facilitating discovery of novel neuroimaging biomarkers.Methods
The prospective tracking system utilized here
consisted of an MR‐compatible camera, designed and built to be mounted
between the transmit (Tx) and receive (Rx) coils of a Nova Medical 2-channel Tx/32-channel Rx head coil, a marker, and a tracking computer which supplies motion updates at
each TR.2 This set-up enables direct line-of-sight to an MR-safe, checkerboard-marker
placed with adhesive on the subject’s forehead allowing the real-time tracking
of subject motion during scanning. All experiments were conducted on a 7T GE MR950 scanner.
To demonstrate proof-of-concept of this PMC system for
in vivo 7T QSM applications, we acquired a 3D coronal multi-echo gradient
echo (mGRE)
(0.35x0.45x1.5mm
resolution, matrix size = 512x384x146, 4 TEs (6.54-27.31 with an echo
spacing of 6.92ms), TR = 34ms, scan time 7min27s) four times on a single healthy,
compliant subject: no motion with and without correction, and with deliberate motion (discrete
rotations ~10-15 degrees to the left or right every 45 seconds) with and
without correction.
For each experimental condition, we performed a
voxel-by-voxel fitting of the signal vs. echo time to compute
R2* maps, and also used the morphology enabled dipole inversion (MEDI) method3 to compute quantitative susceptibility maps. All images were reconstructed at 0.35x0.35x1.5mm resolution. Results
The magnitude images acquired without
deliberate rotational motion show minor motion artifact without correction (Fig. 1A), visibly improved in the
corrected acquisition (Fig. 1C). Deliberate
motion without correction resulted in poor and almost unusable image quality (Fig. 1B). This was significantly
improved with motion-correction,
enabling visualization of deep-gray and brainstem nuclei (Fig. 1D).
A similar trend was seen in the R2* maps (Fig. 2) and QSM maps (Fig. 3). The uncorrected acquisitions
resulted in motion artifact, ranging from minor in the acquisitions without
deliberate rotational motion (Fig. 2A,
3A) to severe in the acquisitions with deliberate motion (Fig. 2B, 3B), with the corrected
acquisitions showing demonstrable visual improvement (Fig. 2C-D, 3C-D).Discussion
Motion-correction for both deliberate and involuntary motion during an mGRE
was successfully demonstrated on human subjects, producing high-quality R2* and
QSM images at 7T.
Qualitative visual improvement in the corrected acquisitions was demonstrated.
Future work will add quantitative assessment of image quality and will extend
the
validation of this PMC system for QSM to additional subjects across a range
of ages and disease conditions. Additionally, because PMC is correcting for
bulk changes in head position and orientation, but not for changes of the head
relative to the magnetic field, the effect of orientation-dependent changes in field
perturbation on the present QSM results needs to be further explored.Conclusion
Our
motion-correction system demonstrates the potential to overcome motion artifact
at 7T, one of the biggest challenges precluding the utilization of
ultra-high-field MR for QSM. Motion artifact was present even in a healthy,
compliant subject, demonstrating the vulnerability of
these sequences to subject motion and underscoring the importance of this
approach. PMC allows for ultra-high-resolution
QSM and R2* mapping that is robust to subject motion, which may facilitate
discovery of novel biomarkers of aging and disease in the brain. We hope to
utilize this technique to analyze QSM changes across hippocampal subfields
during the progression of Alzheimer’s disease and other neurodegenerative
diseases.Acknowledgements
The
authors would like to acknowledge research support by GE Healthcare, NIH P41 EB015891,
NIH S10 RR026351-01A1, and ASNR Boerger Alzheimer’s Fund, NIH R01 1R01AG061120-01.References
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